CN112020373B - Air trap chamber and extracorporeal circulation circuit - Google Patents
Air trap chamber and extracorporeal circulation circuit Download PDFInfo
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- CN112020373B CN112020373B CN201980028249.4A CN201980028249A CN112020373B CN 112020373 B CN112020373 B CN 112020373B CN 201980028249 A CN201980028249 A CN 201980028249A CN 112020373 B CN112020373 B CN 112020373B
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- 230000004087 circulation Effects 0.000 title description 14
- 230000002093 peripheral effect Effects 0.000 claims abstract description 48
- 239000007788 liquid Substances 0.000 claims abstract description 35
- 210000004369 blood Anatomy 0.000 claims description 52
- 239000008280 blood Substances 0.000 claims description 52
- 239000002504 physiological saline solution Substances 0.000 description 11
- 238000000502 dialysis Methods 0.000 description 8
- 238000002637 fluid replacement therapy Methods 0.000 description 8
- 238000011144 upstream manufacturing Methods 0.000 description 8
- 210000003462 vein Anatomy 0.000 description 7
- 238000001514 detection method Methods 0.000 description 6
- 238000005096 rolling process Methods 0.000 description 6
- 239000012510 hollow fiber Substances 0.000 description 5
- 239000012528 membrane Substances 0.000 description 5
- 238000002156 mixing Methods 0.000 description 5
- 230000007423 decrease Effects 0.000 description 4
- 230000037452 priming Effects 0.000 description 4
- 230000017531 blood circulation Effects 0.000 description 3
- 238000010586 diagram Methods 0.000 description 3
- 239000000126 substance Substances 0.000 description 3
- 239000008399 tap water Substances 0.000 description 3
- 235000020679 tap water Nutrition 0.000 description 3
- 208000007536 Thrombosis Diseases 0.000 description 2
- 239000012503 blood component Substances 0.000 description 2
- 230000000052 comparative effect Effects 0.000 description 2
- 239000000306 component Substances 0.000 description 2
- 239000012530 fluid Substances 0.000 description 2
- 238000001631 haemodialysis Methods 0.000 description 2
- 230000000322 hemodialysis Effects 0.000 description 2
- 238000001179 sorption measurement Methods 0.000 description 2
- 230000001154 acute effect Effects 0.000 description 1
- 210000000601 blood cell Anatomy 0.000 description 1
- 210000004204 blood vessel Anatomy 0.000 description 1
- 239000000470 constituent Substances 0.000 description 1
- 238000007599 discharging Methods 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 238000002474 experimental method Methods 0.000 description 1
- 238000011049 filling Methods 0.000 description 1
- 238000001914 filtration Methods 0.000 description 1
- 230000012447 hatching Effects 0.000 description 1
- 238000002615 hemofiltration Methods 0.000 description 1
- 238000001746 injection moulding Methods 0.000 description 1
- 230000014759 maintenance of location Effects 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 238000000746 purification Methods 0.000 description 1
- 239000011347 resin Substances 0.000 description 1
- 229920005989 resin Polymers 0.000 description 1
- 230000000630 rising effect Effects 0.000 description 1
- 239000000243 solution Substances 0.000 description 1
- 239000002904 solvent Substances 0.000 description 1
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 description 1
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
- A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
- A61M1/3621—Extra-corporeal blood circuits
- A61M1/3627—Degassing devices; Buffer reservoirs; Drip chambers; Blood filters
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
- A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
- A61M1/3607—Regulation parameters
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
- A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
- A61M1/3621—Extra-corporeal blood circuits
- A61M1/3627—Degassing devices; Buffer reservoirs; Drip chambers; Blood filters
- A61M1/3638—Degassing devices; Buffer reservoirs; Drip chambers; Blood filters with a vapour trap
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
- A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
- A61M1/38—Removing constituents from donor blood and storing or returning remainder to body, e.g. for transfusion
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
- A61M5/36—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests with means for eliminating or preventing injection or infusion of air into body
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2206/00—Characteristics of a physical parameter; associated device therefor
- A61M2206/10—Flow characteristics
- A61M2206/16—Rotating swirling helical flow, e.g. by tangential inflows
Landscapes
- Health & Medical Sciences (AREA)
- Heart & Thoracic Surgery (AREA)
- Vascular Medicine (AREA)
- Life Sciences & Earth Sciences (AREA)
- Anesthesiology (AREA)
- Biomedical Technology (AREA)
- Engineering & Computer Science (AREA)
- Hematology (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Cardiology (AREA)
- Emergency Medicine (AREA)
- External Artificial Organs (AREA)
- Infusion, Injection, And Reservoir Apparatuses (AREA)
Abstract
In the chamber body (12), liquid flows downward from the inlet (24) to the outlet (31). The introduction pipe (21) is provided so as to extend from an introduction port (24) into the chamber body (12), and an ejection port (23) that is an end opening of the introduction pipe (21) is provided on an inner peripheral surface (26) of the chamber body (12) toward the circumferential direction. As a flow region of the liquid, the chamber body (12) includes: comprises an upper region (41) from the inner surface (28A) of the upper wall (28) to the inlet pipe (21); a lower region (43) connected to the outlet (31); and a connection region (42) connecting the upper region (41) and the lower region (43). The diameter of the inner peripheral surface of the upper region (41) is larger than the diameter of the inner peripheral surface of the lower region (43), and an inclined surface (35A) is formed on the inner peripheral surface of the connecting region (42) by reducing the diameter from the connecting portion with the upper region (41) to the connecting portion with the lower region (43).
Description
Technical Field
The present invention relates to an air trap chamber and an extracorporeal circulation circuit including the air trap chamber.
Background
For example, in hemodialysis, blood drawn from a patient is sent to an extracorporeal circuit. The extracorporeal circulation circuit includes an arterial side circuit for supplying the drawn blood, a purifier (dialyzer) for purifying the blood sent from the arterial side circuit, and a venous side circuit for returning the purified blood to the patient. An air trap chamber for trapping (removing bubbles) air bubbles in blood flowing in the circuit is provided in at least one of the arterial-side circuit and the venous-side circuit.
From the viewpoint of reducing the burden on the patient, the priming volume as the amount of blood drawn from the patient to the extracorporeal circulation circuit is preferably small. Therefore, it can be considered to reduce the volume of the air trap chamber to achieve a reduction in the precharge capacity. However, if the volume of the air trap chamber is extremely small, the bubbles remain in the flow of the blood, i.e., the streaming potential exceeds the buoyancy force acting on the bubbles, and the bubbles may come out of the air trap chamber together with the blood.
For this reason, for example, in patent document 1, a receiving surface is provided immediately below the blood introduction port in a direction orthogonal to the flow of blood, and the flow direction of blood is changed by bringing the blood flow into contact with the contact surface. Thus, by changing the flow of blood in the air trap chamber, the moving distance in the air trap chamber can be increased, and accordingly, air bubbles can be easily trapped.
Prior art literature
Patent literature
Patent document 1: japanese patent application laid-open No. 2016-158921.
Disclosure of Invention
Technical problem to be solved by the invention
However, when the contact surface is arranged so as to be orthogonal to the blood flow, the blood flow is in contact with the contact surface, and therefore the flow velocity is reduced. Thus, blood remains in the air trap chamber. In particular in the lateral flow region remote from the main flow.
It is therefore an object of the present invention to provide an air trap chamber capable of changing the flow direction of a liquid in the air trap chamber while suppressing the attenuation of the flow potential of the liquid flow.
Solution for solving the technical problems
The present invention relates to an air trap chamber. The air trap chamber includes a chamber body and an introduction pipe. The chamber body has a substantially cylindrical shape, one end in the central direction thereof is covered with an upper wall formed with an inlet, and the other end is provided with an outlet from which liquid flows downward to the outlet. The introduction pipe extends from the introduction port into the chamber main body, and the discharge port as an end opening is provided on an inner peripheral surface of the chamber main body in a circumferential direction. As a flow area of the liquid, the chamber body includes: comprises an upper region from the inner surface of the upper wall to the ingress pipe, a lower region connected with the egress port, and a connection region connecting the upper region and the lower region. The diameter of the inner peripheral surface of the upper region is larger than that of the inner peripheral surface of the lower region, and an inclined surface is formed on the inner peripheral surface of the connecting region by reducing the diameter from the connecting portion with the upper region to the connecting portion with the lower region.
According to the above invention, the liquid is ejected from the ejection port along the inner peripheral surface of the chamber body. The ejected liquid flow forms a swirling flow along the inner peripheral surface of the chamber body, and is directed to the guide outlet. Here, since the inner peripheral surface of the connection region is an inclined surface, at least a part of the swirling flow changes its flow direction along the inclined surface. When the flow direction is changed, an inclined surface is formed along the flow direction of the swirling flow, so that the flow potential of the liquid flow is maintained.
In the above invention, the inner peripheral surface of the connection region may have a truncated conical shape including a vertical surface parallel to the inner peripheral surface of the upper region.
The inner peripheral surface of the connecting region is formed in a single truncated cone shape including a vertical surface parallel to the inner peripheral surface of the upper region, and gradually slopes from the inner peripheral surface of the upper region to the inclined surface of the connecting region in the circumferential direction. By continuously inclining in this manner, the swirling flow flowing on the inner peripheral surface of the upper region smoothly shifts to the inclined surface, and the direction of flow can be changed on the inclined surface while maintaining the flow potential.
In the above invention, the angle of the inclined surface with respect to the plane perpendicular to the opening axis of the outlet may be more than 0 ° and less than 90 °.
In the above invention, the angle of the inclined surface with respect to the plane perpendicular to the opening axis of the outlet may be 25 ° or more and 72 ° or less.
By setting the inclined surface within the above-described angle range, leakage of bubbles escaping from the outlet port is suppressed.
In the above invention, the inclined surface may be a concave curved surface protruding radially outward from the central axis of the chamber body.
In the above invention, the inclined surface may be a convex curved surface protruding radially inward with the central axis of the chamber body as a base point.
In addition, the invention relates to an extracorporeal circuit. In this circuit, the drawn blood is circulated. The air trap chamber according to the above invention is connected to the flow path of the extracorporeal circulation circuit.
Effects of the invention
According to the present invention, the flow direction of the liquid in the air trap chamber can be changed while suppressing the attenuation of the flow potential of the liquid flow.
Drawings
Fig. 1 is a diagram illustrating an extracorporeal circulation circuit using an air trap chamber according to the present embodiment.
Fig. 2 is a perspective view illustrating an air trap chamber according to the present embodiment.
Fig. 3 is a perspective cross-sectional view illustrating an air trap chamber according to the present embodiment.
Fig. 4 is a diagram illustrating a structure of a cover of an air trap chamber according to the present embodiment.
Fig. 5 is a perspective exploded view showing an example in which the air trap chamber according to the present embodiment is decomposed into a cover and a case.
Fig. 6 is a perspective view illustrating an inclined surface of a tapered portion constituting a connection region.
Fig. 7 is a cross-sectional view A-A of fig. 2.
Fig. 8 is a perspective cross-sectional view illustrating a state when the air trap chamber according to the present embodiment is used.
Fig. 9 is a diagram illustrating the overall flow in the air trap chamber according to the present embodiment.
Fig. 10 is a cross-sectional view A-A of fig. 2, and is a view illustrating the overall flow in the air trap chamber according to the present embodiment.
Fig. 11 is a view illustrating the same cut surface as the A-A cross-sectional view of fig. 2 for a first other example (an inclination angle of 25 °) of the air trap chamber according to the present embodiment.
Fig. 12 is a view illustrating the same cut surface as the A-A cross-sectional view of fig. 2 for a second other example of the air trap chamber (inclination angle 58 °).
Fig. 13 is a view illustrating the same cut surface as the A-A cross-sectional view of fig. 2 in a third other example of the air trap chamber (tilt angle 72 °).
Fig. 14 is a view illustrating the same cut surface as the A-A cross-sectional view of fig. 2 of the air trap chamber (inclination angle 0 °) according to the comparative example.
Fig. 15 is a view illustrating a cut surface similar to the A-A cross-sectional view of fig. 2 in a fourth other example (concave surface) of the air trap chamber according to the present embodiment.
Fig. 16 is a view illustrating the same cut surface as the A-A cross-sectional view of fig. 2 in a fifth other example (convex surface) of the air trap chamber according to the present embodiment.
Detailed Description
Fig. 1 illustrates an extracorporeal circuit to which an air trap chamber 10 according to the present embodiment is connected. The extracorporeal circulation circuit is, for example, a circuit for hemodialysis, and includes an arterial side circuit 50, a blood purifier 54, a dialysis device 55, a venous side circuit 51, and a fluid replacement line 60. The air trap chamber 10 according to the present embodiment is connected to an extracorporeal circuit for dialysis treatment, but is not limited to this embodiment. For example, the air trap chamber 10 according to the present embodiment may be connected to an extracorporeal circulation circuit that can circulate blood drawn from a patient and perform purification treatment. For example, the air trap chamber 10 according to the present embodiment may be connected to an extracorporeal circulation circuit used for Acetate-Free Biofiltration (AFBF), continuous slow hemofiltration, blood adsorption, selective blood cell component removal, simple plasma exchange, double filtration plasma exchange, plasma adsorption, or the like. The air trap chamber 10 according to the present embodiment may be provided in an arterial-side circuit 50, a venous-side circuit 51, and a fluid supply line 60, which will be described later, of the extracorporeal circulation circuit. In addition, the air trap chamber 10 according to the present embodiment may be connected to a path along which thrombus may occur, that is, a path along which blood or a blood component flows in the extracorporeal circulation circuit. The air trap chamber 10 according to the present embodiment may be connected to a path through which blood or a blood component of the extracorporeal circuit flows, a path through which physiological saline flows, and a path including these extracorporeal circuits.
Blood drawn from the patient is supplied to the arterial circuit 50. The arterial circuit 50 is provided with an arterial puncture needle 52 and a rolling pump 53 from the upstream side. The arterial side puncture needle 52 pierces a blood vessel of the patient and sends blood into a tube of the arterial side circuit 50 (blood drawing-out).
The rolling pump 53 smoothes the tube from the outside of the tube, thereby transferring the blood in the tube to the blood purifier 54. In addition, for example, when priming is performed, since the priming liquid may be filled into the circuit from the venous side circuit, the rolling pump 53 may be rotated in the forward and reverse directions.
The air trap chamber 10 according to the present embodiment may be connected between the arterial puncture needle 52 and the rolling pump 53, and between the rolling pump 53 and the blood purifier 54. The structure and function of the air trap chamber 10 will be described later. In order to reliably remove air bubbles in blood during the back transfusion, the air trap chamber 10 in the venous side circuit 51 is a necessary structure, and the air trap chamber 10 provided in the arterial side circuit 50 may be provided arbitrarily.
A fluid supply line 60 is provided between the rolling pump 53 of the arterial circuit 50 and the blood purifier 54. A fluid replacement bag 57 and a clamp 59 are provided in the fluid replacement line 60. An air trap chamber 10 is provided between the fluid replacement bag 57 and the jig 59.
The fluid replacement bag 57 contains physiological saline as fluid replacement. For example, when the extracorporeal circulation circuit is to be refilled, the clamp 59 is opened, and physiological saline flows from the fluid replacement bag 57 into the extracorporeal circulation circuit. The bubbles in the circuit are removed by filling the circuit with physiological saline. When the priming is completed, the clamp 59 is switched to the closed state.
After the dialysis treatment is completed, the clamp 59 is opened again to return the blood in the circuit to the patient, and the circuit is filled with the physiological saline in the fluid replacement bag 57. In other words, the blood in the circuit is replaced with physiological saline.
The blood purifier 54 purifies blood sent from the arterial side circuit 50. The blood purifier 54 is a so-called dialyzer, for example, in which dialysate and blood exchange substances via a hollow fiber membrane 54A. The blood purifier 54 accommodates bundles of a plurality of hollow fiber membranes 54A (hollow fiber membrane bundles) inside the column 54B.
The column 54B is a cylindrical accommodating member, and has an inlet side cover 54C attached to one end in the center axis direction and an outlet side cover 54D attached to the other end. A blood introduction port 54E connected to a connector (not shown) at the downstream end of the arterial side circuit 50 is provided in the introduction side cover 54C. The outlet side cover 54D is provided with a blood outlet port 54F connected to a connector (not shown) at the upstream end of the venous side circuit 51. The blood sent from the arterial-side circuit 50 flows into the hollow fiber membrane 54A from the blood introduction port 54E.
A dialysate introduction port 54G is provided in a portion of the column 54B near the outlet-side cover 54D. In addition, a dialysate outlet port 54H is provided in a portion of the column 54B near the inlet-side cover 54C. Dialysate is delivered from the dialysis device 55 into the column 54B via the dialysate introduction port 54G. The dialysate and blood exchange substances through the hollow fiber membranes 54A, and as a result, the blood is purified. The dialysate after the substance exchange is returned to the dialysis device 55 via the dialysate outlet port 54H. The purified blood is sent to the venous-side circuit 51 through the blood outlet port 54F.
In the venous side circuit 51, the purified blood is returned to the patient via the venous side puncture needle 56. In order to remove (debubble) air bubbles in blood at the time of back transfusion, an air trap chamber 10 is provided in the venous side circuit 51.
Fig. 2 illustrates an air trap chamber 10 according to the present embodiment. In addition, fig. 3 illustrates a perspective cross-sectional view of the air trap chamber 10. The air trap chamber 10 includes a chamber body 12 and a filter 40.
In the dialysis treatment, the air trap chamber 10 is used in a state of being erected with the upper side of the drawing sheet being up and the lower side of the drawing sheet being down. Hereinafter, the position and structure of each constituent will be described with reference to the upright arrangement at the time of use unless otherwise specified.
The chamber body 12 is substantially cylindrical in shape, and one end (upper end) in the direction of its center axis C1 is covered with an upper wall 28. The upper wall 28 is provided with an inlet 24 and an exhaust port 22. The chamber body 12 is provided with an outlet 31 at the other end (lower end) in the direction of the central axis C1. That is, in the chamber main body 12, the liquid (blood, physiological saline, etc.) flows downward from the inlet 24 to the outlet 31.
As shown in fig. 7 described later, the air trap chamber 10 according to the present embodiment has a structure in which the opening axis C2 of the inlet port 24, the central axes C3 of the first and second connection flanges 27 and 32, and the opening axis C1 of the delivery pipe 33 are disposed out of the axis. Therefore, any one of the three can be used as the central axis of the air trap chamber 10, but in the following, the opening axis C1 of the delivery tube 33 is used as the central axis of the air trap chamber 10 for convenience. Since the opening axes C1, C2 and the central axis C3 are all provided to extend parallel to each other, the positional relationship between one end (upper end) and the other end (lower end) along any axis is substantially unchanged.
For example, as shown in fig. 5, the chamber body 12 may be constituted by a cover 20 as an upper member and a housing 30 as a lower member. The cover 20 and the case 30 are obtained by, for example, injection molding resin.
Fig. 4 illustrates a perspective cross-sectional view of the cover 20. The cover 20 is a U-shaped cross-section member having an inlet pipe 21 and an outlet port 22 at its upper end (one end). Cover 20 includes upper wall 28, cover body 25, first connection flange 27, and introduction tube 21.
The lid main body 25 is a liquid receiving portion whose inner surface is in contact with liquid, and is formed in a cylindrical shape in which one end (upper end) of the chamber main body 12 in the central axis C1 direction is closed by an upper wall 28. An inlet 24 (see fig. 3) and an exhaust port 22 are formed in the upper wall 28. In addition, the other end (lower end) of the cover main body 25 is connected to the first connection flange 27. The first connecting flange 27 is the other end (lower end) of the cover 20 in the direction of the central axis C1.
Further, introduction tube 21 is extended from upper wall 28 to the inside of lid main body 25, that is, the inside of chamber main body 12. When the air trap chamber 10 is provided in the vein side circuit 51, an introduction port 24 connected to a pipe on the upstream side of the vein side circuit 51 by adhesion of a solvent or the like is formed at the upper end of the introduction pipe 21. Further, a discharge port 23 for discharging liquid into the chamber body 12 is formed at the lower end of the introduction pipe 21. By providing the ejection port 23 below the inner surface 28A of the upper wall 28 in this way, bubbles in the chamber body 12 are prevented from escaping from the introduction pipe 21 to bubbles on the upstream side of the vein side circuit 51.
That is, for example, when the ejection port 23 is provided on the inner surface 28A of the upper wall 28, that is, at the same height as the exhaust port 22, there is a possibility that bubbles in the chamber move to the ejection port 23 without entering the exhaust port 22 and escape directly to the upstream side of the vein side circuit 51. Therefore, in the air trap chamber 10 according to the present embodiment, the air bubbles are prevented from being mixed into the upstream side of the vein side circuit 51 by lowering the ejection port 23 into the chamber.
The discharge port 23 of the introduction pipe 21 is provided along the inner peripheral surface 26 of the cap main body 25, and its opening is directed in the circumferential direction of the inner peripheral surface 26. For example, a lower wall 21A is formed at the lower end of introduction tube 21, and the side surface thereof is cut off to form discharge port 23. For example, the ejection orifice 23 is oriented parallel to the tangential direction of the inner peripheral surface 26. The cut surface 21B of the discharge port 23 is formed parallel to the radial direction of the inner peripheral surface 26.
The discharge port 23 is provided on the inner peripheral surface 26 of the cap body 25 in the circumferential direction, and thereby the flow of the liquid (blood, physiological saline, etc.) flowing out from the discharge port 23 becomes a swirling flow flowing along the inner peripheral surface 26. The liquid flow in the air trap chamber 10 becomes a swirling flow, and thus, the liquid retention in the air trap chamber 10 is suppressed as compared with the case where a specific flow is not formed.
A first flange 27 is connected to the lower end of the cover main body 25. The first flange 27 is, for example, a cylindrical member coaxial with the cover main body 25, and is formed to have an inner diameter larger than that of the cover main body 25 (expanded diameter).
Referring to fig. 3, 5, and 7, the housing 30 is a substantially cylindrical member, and has a second connection flange 32 formed at one end (upper end) along the central axis C1 of the chamber body 12 and a delivery tube 33 formed at the other end (lower end). The lower end of the delivery tube 33 is a delivery port 31. The outlet port 31 is connected to a connector (not shown) at the upstream end of the vein side circuit 51, and guides the liquid (blood, physiological saline, etc.) in the air trap chamber 10 to the vein side circuit 51.
The housing 30 is provided with a second connection flange 32, a tapered portion 35, a housing body 34, and a delivery tube 33 in this order from the lid 20 side toward the lower side.
The second connection flange 32 is a cylindrical portion fitted with the first connection flange 27 of the cover 20. For example, as shown in fig. 3 and 7, the first connecting flange 27 of the cover 20 is fitted to the second connecting flange 32 of the housing 30 so that the inner peripheral surface thereof faces the outer peripheral surface thereof. For example, the inner diameter D1 of the second connecting flange 32 is formed to be equal to the inner diameter of the cover main body 25. In addition, the inner diameter D1 of the second connection flange 32 is formed to be larger than the inner diameter D2 of the housing main body 34.
Note that, when the inner peripheral surface of the second connecting flange 32 and the inner peripheral surface of the housing main body 34 are tapered in shape in which the diameters decrease as approaching the outlet port 31, the maximum diameters thereof may be set to the inner diameters D1, D2.
The housing body 34 is, for example, an elongated cylindrical portion extending in the direction of the central axis C1 of the chamber body 12. A filter 40 attached to the delivery tube 33 and capturing a fixed object such as thrombus is accommodated in the housing main body 34. A delivery tube 33 is connected to the lower end of the housing main body 34.
A tapered portion 35 is formed between the second connection flange 32 and the housing main body 34. The tapered portion 35 is a connecting portion connecting the second connecting flange 32 having a relatively large diameter and the housing main body 34 having a relatively small diameter. As its name suggests, the taper 35 tapers in diameter from the second connection flange 32 to the housing body 34. Specifically, the tapered portion 35 gradually decreases in inner diameter from an inner diameter D1 at an upper end thereof, i.e., a connection portion with the second connection flange 32, to an inner diameter D2 at a lower end thereof, i.e., a connection portion with the housing main body 34. As will be described later, the connection region 42 is divided by the taper portion 35.
As shown in fig. 6 and 7, the inner peripheral surface of the tapered portion 35 (and thus the connection region 42) may be of a one-sided tapered shape in cross section. That is, a region in which the inclined surface 35A is formed along the circumferential direction and a region interrupted by the inclined surface 35A and becoming a vertical surface 35B parallel to the inner peripheral surface of the second connecting flange 32 (and thus the upper region 41) may be formed.
Fig. 6 shows an example in which the second connection flange 32 is removed from the housing 30. As shown in the drawing, the inner peripheral surface of the tapered portion 35 is formed in a truncated conical shape including a vertical surface 35B.
For example, consider that an X-axis passing through the center of the cross-sectional circle thereof from a position where the vertical surface 35B is formed, an inclined surface is formed from the vertical surface 35B along the circumferential direction to the inner surface thereof, and the inclination angle along the place where the X-axis is opposed to the vertical surface 35B is an acute angle closest to the X-axis. In other words, since the central axis C1 of fig. 3 is orthogonal to the X axis, the inclination angle of the point is an angle in which an axis or a plane perpendicular to the central axis C1 is placed.
In this way, the inner peripheral surface of the tapered portion 35 is formed in a shape gradually inclined (inclined surface is placed) in the circumferential direction from the vertical surface 35B, so that the flow of the swirling flow flowing along the inner peripheral surface of the lid main body 25 is smoothly guided to the inclined surface 35A. Thus, for example, compared with a case where a wall orthogonal to the flow direction is provided, the direction of the flow can be changed by the inclined surface 35A of the tapered portion 35 while maintaining the flow potential of the swirling flow.
In addition, in the case where the inclined surface 35A is provided on a part of the circumferential direction, the latter can make the angle of the inclined surface 35A more gentle (inclined to the horizontal side) under the condition that the inner diameter D1 of the upper region 41 and the inner diameter D2 of the lower region 43 are constant, as compared with the case where the inclined surface 35A is provided on the inner circumferential surface of the tapered portion 35 over the entire circumference.
Note that, as an index indicating the inclination of the inclined surface, the maximum inclination angle of the tapered portion 35 is represented as an inclination angle α. That is, the angle opposite to the axis perpendicular to the central axis C1 and the plane of the chamber body 12 is set as the inclination angle α. Fig. 7 illustrates a cross-sectional view A-A of fig. 2 including a maximum inclination angle α of the tapered portion 35. In the example shown in this figure, the inclination angle α=42°.
Further, since the diameter of the tapered portion 35 is unevenly reduced in the radial direction from the second connection flange 32 to the case main body 34, the opening axis C2 of the inlet pipe 21 and the opening axis C1 of the outlet pipe 33 of the cap 20 can be disposed out of the axis.
That is, as described above, opening axis C2 of introduction tube 21 is disposed out of the axis with respect to the center axis C3 of first connecting flange 27, which is the center axis of cover 20. Further, since the diameter of the tapered portion 35 is unevenly reduced in the radial direction, the opening axis C1 of the delivery tube 33 may be disposed out of the axis with respect to the central axis C3 of the second connection flange 32.
For example, as shown in fig. 7, when the opening axis C2 of the introduction pipe 21 and the opening axis C1 of the delivery pipe 33 are arranged in parallel on the same plane with the central axis C3 of the first and second connection flanges 27 and 32 interposed therebetween, the opening axis C2 of the introduction pipe 21 and the opening axis C1 of the delivery pipe 33 are separated in the vertical direction.
Since opening axis C2 of introduction tube 21 is offset from opening axis C1 of delivery tube 33, bubbles flowing backward from delivery tube 33 are prevented from entering introduction tube 21 when rising due to buoyancy. As a result, the reverse flow of bubbles is suppressed from entering the arterial side circuit 50 and the blood purifier 54 upstream of the air trap chamber 10.
Referring to fig. 7, the chamber body 12 is divided into a plurality of regions as regions in which liquid (blood, physiological saline, etc.) flows according to the structures, in particular, the inner diameters, of the respective parts of the cover 20 and the housing 30. Specifically, the cover 20 may be divided into an upper region 41, a connection region 42, and a lower region 43.
The upper region 41 is a region including from the inner surface 28A of the upper wall 28 of the cover 20 to the introduction pipe 21, and is a region divided by the upper wall 28, the cover main body 25, and the second connection flange 32 of the case 30. The diameter D1 (inner diameter) of the inner peripheral surface of this region is larger than the inner diameter D2 (D1 > D2) of the lower region 43.
The lower region 43 is a region connected to the delivery tube 33, and is divided by the housing main body 34. The inner diameter D2 of the lower region 43 is smaller than the inner diameter D1 of the upper region 41.
The connection region 42 is a region connecting the upper region 41 and the lower region 43, and is divided by the tapered portion 35 of the housing 30. The diameter of the inner peripheral surface thereof gradually decreases along the inclined surface 35A from the inner diameter D1 of the connecting portion with the upper region 41 to the inner diameter D2 of the connecting portion with the lower region 43.
< flow of liquid in air trap Chamber >
The flow of the liquid (blood, physiological saline, etc.) in the air trap chamber 10 according to the present embodiment will be described with reference to fig. 8 to 10. Fig. 8 illustrates the state of the air trap chamber 10 at the time of dialysis treatment. The air trap chamber 10 may be a so-called airless chamber in which the upper region 41, the connection region 42, and the lower region 43 of the internal space of the chamber body 12 are filled with liquid as shown by the broken line hatching in the drawing.
In this way, in a state where the chamber body 12 is filled with the liquid, the liquid further flows in from the ejection port 23. As described above, since the discharge ports 23 are provided on the inner peripheral surface 26 of the cap 20 in the circumferential direction, the flow of the liquid flowing in from the discharge ports 23 becomes a swirling flow along the inner peripheral surface 26 of the upper region 41 as shown by the solid line in fig. 9.
The swirling liquid flows from the upper region 41 into the connection region 42 along the inner peripheral surface 26. At this time, along the inclined surface 35A of the connection region 42, the flow direction of at least a part of the swirling flow is changed. Specifically, due to the diameter reduction in the connecting region 42 and the orientation of the inclined surface 35A, an upward swirling flow component is generated as shown by the broken line in fig. 9 and 10.
By generating an upward swirling flow, the liquid exchange in the upper region 41, particularly above the discharge port 23, is promoted. By generating an upward swirling flow by the inclined surface 35A in this way, stagnation of the liquid in a portion above the discharge port 23 in the upper region 41 is suppressed.
In addition, when the flow direction on the inclined surface 35A is changed, the inclined surface 35A is formed to be gradually inclined in the circumferential direction from the vertical surface 35B continuous with the inner peripheral surface 26 of the upper region 41 as described above. Therefore, the liquid smoothly flows from the inner peripheral surface 26 to the inclined surface 35A, and an upward swirling flow can be generated from at least a part of the flow while maintaining the flow potential.
< air trap Chamber according to other example of the present embodiment >
In the above embodiment, the inclination angle α of the tapered portion 35 was set to 42 °, but various modifications are possible in addition to this. For example, as described above, since the flow direction of at least a part of the swirling flow is changed along the inclined surface 35A, it is sufficient to qualitatively make 0 ° < α <90 °. For example, in the first other example shown in fig. 11, the inclination angle α=25°. In addition, in the second other example shown in fig. 12, the inclination angle α=58°. Further, in the first other example shown in fig. 13, the inclination angle α=72°.
In these first to third other examples, since the inclined surface 35A is provided between the upper region 41 and the lower region 43 as in the embodiment shown in fig. 10, at least a part of the liquid flowing from the inner peripheral surface 26 can be made into an upward swirling flow while the decline of the flow potential of the liquid flowing from the inner peripheral surface 26 is suppressed by using the inclined surface 35A.
Here, when the volume of the air trap chamber 10 according to the present embodiment and the first to third other examples is reduced, it is necessary to prevent leakage of air bubbles escaping from the outlet port 31. Accordingly, the present inventors have conducted experiments on the air trap chamber 10 according to the present embodiment and the first to third other examples, as to whether or not there is a bubble leakage.
In the test, the capacity (precharge capacity, hereinafter referred to as PV) of the air-trap chamber 10 according to the first other example (α=25°) was set to 16.3mL. The PV of the air trap chamber 10 according to the present embodiment was set to 16.5mL. In addition, the PV of the air trap chamber 10 related to the second other example (α=58°) was set to 16.9mL. Further, the PV of the air trap chamber 10 related to the third other example (α=72°) was set to 17.6mL.
In the above test, as a comparative example, as shown in fig. 14, an air trap chamber 10 having no inclined surface 35A was prepared. The PV of the chamber was set to 16.0mL.
In the test, tap water from which bubbles were removed was supplied to the inlet 24 of each air trap chamber 10 using a roll pump. The supply amounts were both 400mL/min and 600 mL/min.
Further, air is mixed into the air trap chamber 10 from the air outlet 22 using a syringe. The mixing amount of air was 0.3. Mu.L and 15. Mu.L with respect to each air trap chamber 10. When air is mixed into the air trap chamber 10, the running water flow is temporarily stopped, and after mixing, the supply of tap water is restarted.
In addition, the bubble detecting means is connected to the outlet port 31 of the air trap chamber 10. Then, three tests were performed on each air trap chamber 10 according to the supply amount of tap water and the mixing amount of air, and it was checked whether or not the air bubble was detected by the air bubble detecting means. In addition, when the air mixing amount of the syringe is 0.3 μl, the threshold value of the air bubble detection signal of the air bubble detection means is set to 0.3 μl, and when the air mixing amount is 15 μl, the threshold value of the air bubble detection signal of the air bubble detection means is set to 15 μl. The test results are shown in table 1 below.
[ Table 1 ]
In table 1, symbol o indicates that no detection signal was output from the bubble detector in all of the three tests, and symbol x indicates that no detection signal was output from the bubble detector in any of the three tests. As shown in table 1, in the air trap chamber 10 according to the present embodiment and the first to third other examples, the air bubbles can be effectively prevented from leaking by setting the inclination angle α to 25 ° or more and 72 ° or less.
Note that, in the above embodiment, the inclined surface 35A of the tapered portion 35 which is the connection region 42 is made linear in cross section, but the present invention is not limited to this configuration. For example, as in the fourth other example shown in fig. 15, the inclined surface 35A may be a concave curved surface protruding radially outward from the central axis C1 of the chamber body 12. As in the fifth other example shown in fig. 16, the inclined surface 35A may be a convex curved surface protruding radially inward with the central axis C1 of the chamber body 12 as a base point.
When the inclined surface 35A is formed into a concave curved surface or a convex curved surface, the inclination angle α thereof may be defined as follows. That is, the upper end of the tapered portion 35, that is, the point of the inclined surface 35A at the boundary with the upper region 41, and the lower end of the tapered portion 35, that is, the point of the inclined surface 35A at the boundary with the lower region 43 are connected. The angle of the straight line thus obtained with respect to the axis and the plane perpendicular to the central axis C1 of the chamber body 12 is set as the inclination angle α. In this definition, the preferable range of the inclination angle α when the inclined surface 35A is made to be a concave curved surface or a convex curved surface is preferably more than 0 ° and less than 90 °. Further, the preferable range of the inclination angle α is more preferably 25 ° or more and 72 ° or less.
Description of the reference numerals
10 air trap chamber, 12 chamber body, 20 cap, 21 introduction tube, 22 exhaust port, 23 exhaust port, 24 introduction port, 25 cap body, 26 inner peripheral surface of upper region, 27 first connection flange, 28 cap body upper wall, 28A upper wall inner surface, 30 housing, 31 outlet port, 32 second connection flange, 33 delivery tube, 34 housing body, 35 taper portion, 35A inclined surface, 35B vertical surface, 40 filter, 41 upper region, 42 connection region, 43 lower region, 50 arterial side circuit, 51 venous side circuit, 54 blood purifier, 55 dialysis apparatus.
Claims (6)
1. An air trap chamber, comprising:
a chamber body having a substantially cylindrical shape, one end in a central axis direction of the chamber body being covered with an upper wall formed with an inlet, and an outlet being provided at the other end, the liquid flowing downward from the inlet to the outlet; and
an introduction pipe extending from the introduction port into the chamber main body, wherein an ejection port as an end opening is provided on an inner peripheral surface of the chamber main body toward a circumferential direction,
as a flow area of the liquid, the chamber body includes:
comprising an upper region from an inner surface of the upper wall to the ingress pipe;
a lower region connected to the outlet; and
a connection region connecting the upper region and the lower region,
the diameter of the inner peripheral surface of the upper region is larger than the diameter of the inner peripheral surface of the lower region,
an inclined surface is formed on the inner peripheral surface of the connection region by reducing the diameter from the connection portion with the upper region to the connection portion with the lower region;
the inner peripheral surface of the connecting region is in a truncated conical shape including a vertical surface parallel to the inner peripheral surface of the upper region;
the opening shaft of the inlet, the opening shaft of the outlet, and the central axis of the upper region are disposed outside the shaft.
2. The air trap chamber according to claim 1, wherein,
the inclined surface has an angle exceeding 0 DEG and less than 90 DEG with respect to a plane perpendicular to an opening axis of the outlet.
3. The air trap chamber according to any one of claim 1 or 2, wherein,
the inclined surface has an angle of 25 DEG to 72 DEG with respect to a plane perpendicular to the opening axis of the outlet.
4. The air trap chamber according to claim 1, wherein,
the inclined surface is a concave curved surface protruding radially outward from a central axis of the chamber body.
5. The air trap chamber according to claim 1, wherein,
the inclined surface is a convex curved surface protruding radially inward with a central axis of the chamber body as a base point.
6. An extracorporeal circuit in which the air trap chamber according to any one of claims 1 to 5 is connected to a flow path of an extracorporeal circuit for circulating blood.
Applications Claiming Priority (3)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP2018-088657 | 2018-05-02 | ||
| JP2018088657A JP6539379B1 (en) | 2018-05-02 | 2018-05-02 | Air trap chamber and extracorporeal circulation circuit |
| PCT/JP2019/010960 WO2019211951A1 (en) | 2018-05-02 | 2019-03-15 | Air trap chamber and extracorporeal circulation circuit |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN112020373A CN112020373A (en) | 2020-12-01 |
| CN112020373B true CN112020373B (en) | 2023-11-28 |
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Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201980028249.4A Active CN112020373B (en) | 2018-05-02 | 2019-03-15 | Air trap chamber and extracorporeal circulation circuit |
Country Status (5)
| Country | Link |
|---|---|
| US (1) | US20210093774A1 (en) |
| EP (1) | EP3789059B1 (en) |
| JP (1) | JP6539379B1 (en) |
| CN (1) | CN112020373B (en) |
| WO (1) | WO2019211951A1 (en) |
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2018
- 2018-05-02 JP JP2018088657A patent/JP6539379B1/en active Active
-
2019
- 2019-03-15 CN CN201980028249.4A patent/CN112020373B/en active Active
- 2019-03-15 US US17/050,768 patent/US20210093774A1/en active Pending
- 2019-03-15 WO PCT/JP2019/010960 patent/WO2019211951A1/en unknown
- 2019-03-15 EP EP19796954.6A patent/EP3789059B1/en active Active
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|---|---|---|---|---|
| DE3202582A1 (en) * | 1981-01-29 | 1982-09-09 | INFUS Hospitalbedarf GmbH & Co Vertriebs KG, 8017 Ebersberg | Drip chamber for monitoring blood in an extracorporeal circulation in haemodialysis by means of an artificial kidney |
| US5328461A (en) * | 1992-04-30 | 1994-07-12 | Utterberg David S | Blow molded venous drip chamber for hemodialysis |
| US5849065A (en) * | 1996-04-27 | 1998-12-15 | Fresenius Ag | Device for separating gas bubbles from fluids, in particular blood |
| US6013061A (en) * | 1997-10-15 | 2000-01-11 | Microwave Medical Systems, Inc. | Automatic air eliminator |
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Also Published As
| Publication number | Publication date |
|---|---|
| JP2019193734A (en) | 2019-11-07 |
| EP3789059A1 (en) | 2021-03-10 |
| US20210093774A1 (en) | 2021-04-01 |
| EP3789059B1 (en) | 2024-02-28 |
| CN112020373A (en) | 2020-12-01 |
| WO2019211951A1 (en) | 2019-11-07 |
| EP3789059A4 (en) | 2022-01-05 |
| JP6539379B1 (en) | 2019-07-03 |
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